[go: up one dir, main page]

EP0075606A1 - Système pour la circulation extracorporelle du sang - Google Patents

Système pour la circulation extracorporelle du sang Download PDF

Info

Publication number
EP0075606A1
EP0075606A1 EP81107648A EP81107648A EP0075606A1 EP 0075606 A1 EP0075606 A1 EP 0075606A1 EP 81107648 A EP81107648 A EP 81107648A EP 81107648 A EP81107648 A EP 81107648A EP 0075606 A1 EP0075606 A1 EP 0075606A1
Authority
EP
European Patent Office
Prior art keywords
blood
detecting
line
pressure
upper limit
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Granted
Application number
EP81107648A
Other languages
German (de)
English (en)
Other versions
EP0075606B1 (fr
Inventor
Tsunekazu Hino
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Hino Tsunekazu
Omron Corp
Original Assignee
Omron Tateisi Electronics Co
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority to US06/305,381 priority Critical patent/US4466804A/en
Application filed by Omron Tateisi Electronics Co filed Critical Omron Tateisi Electronics Co
Priority to EP88106528A priority patent/EP0309642A1/fr
Priority to EP81107648A priority patent/EP0075606B1/fr
Priority to DE8181107648T priority patent/DE3175734D1/de
Priority to EP84114264A priority patent/EP0150314A3/fr
Priority claimed from EP84114264A external-priority patent/EP0150314A3/fr
Publication of EP0075606A1 publication Critical patent/EP0075606A1/fr
Application granted granted Critical
Publication of EP0075606B1 publication Critical patent/EP0075606B1/fr
Expired legal-status Critical Current

Links

Images

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
    • A61M1/3621—Extra-corporeal blood circuits
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
    • A61M1/3621—Extra-corporeal blood circuits
    • A61M1/3623—Means for actively controlling temperature of blood
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
    • A61M1/3621—Extra-corporeal blood circuits
    • A61M1/3624—Level detectors; Level control
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/10—Location thereof with respect to the patient's body
    • A61M60/104—Extracorporeal pumps, i.e. the blood being pumped outside the patient's body
    • A61M60/109—Extracorporeal pumps, i.e. the blood being pumped outside the patient's body incorporated within extracorporeal blood circuits or systems
    • A61M60/113—Extracorporeal pumps, i.e. the blood being pumped outside the patient's body incorporated within extracorporeal blood circuits or systems in other functional devices, e.g. dialysers or heart-lung machines
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/20—Type thereof
    • A61M60/247—Positive displacement blood pumps
    • A61M60/253—Positive displacement blood pumps including a displacement member directly acting on the blood
    • A61M60/268—Positive displacement blood pumps including a displacement member directly acting on the blood the displacement member being flexible, e.g. membranes, diaphragms or bladders
    • A61M60/279—Peristaltic pumps, e.g. roller pumps
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/30—Medical purposes thereof other than the enhancement of the cardiac output
    • A61M60/36—Medical purposes thereof other than the enhancement of the cardiac output for specific blood treatment; for specific therapy
    • A61M60/38—Blood oxygenation
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/40—Details relating to driving
    • A61M60/424—Details relating to driving for positive displacement blood pumps
    • A61M60/438—Details relating to driving for positive displacement blood pumps the force acting on the blood contacting member being mechanical
    • A61M60/441—Details relating to driving for positive displacement blood pumps the force acting on the blood contacting member being mechanical generated by an electromotor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/50—Details relating to control
    • A61M60/508—Electronic control means, e.g. for feedback regulation
    • A61M60/515—Regulation using real-time patient data
    • A61M60/531—Regulation using real-time patient data using blood pressure data, e.g. from blood pressure sensors
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/80—Constructional details other than related to driving
    • A61M60/845—Constructional details other than related to driving of extracorporeal blood pumps
    • A61M60/851—Valves
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/3303—Using a biosensor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/3331—Pressure; Flow
    • A61M2205/3337—Controlling, regulating pressure or flow by means of a valve by-passing a pump
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/3331—Pressure; Flow
    • A61M2205/3344—Measuring or controlling pressure at the body treatment site
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/3331—Pressure; Flow
    • A61M2205/3351—Controlling upstream pump pressure
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/3331—Pressure; Flow
    • A61M2205/3355—Controlling downstream pump pressure
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/3379—Masses, volumes, levels of fluids in reservoirs, flow rates
    • A61M2205/3382—Upper level detectors
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/3379—Masses, volumes, levels of fluids in reservoirs, flow rates
    • A61M2205/3386—Low level detectors
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10S—TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10S128/00—Surgery
    • Y10S128/03—Heart-lung

Definitions

  • the present invention relates to a system for the extracorporeal circulation of the blood for a patient undergoing an operation on the lung or heart to refresh the blood of the patient and always circulate the blood through the body in place of the lungs and heart of the patient.
  • Systems for extracorporeally circulating the blood comprise a blood withdrawing line for drawing off the venous blood from the patient, an artificial lung provided on the line, a reservoir for the withdrawn blood, a blood supply line for feeding the blood from the reservoir to the artery of the patient, and a blood supply pump provided on the blood supply line and serving as an artificial heart.
  • a blood withdrawing line for drawing off the venous blood from the patient
  • an artificial lung provided on the line
  • a reservoir for the withdrawn blood
  • a blood supply line for feeding the blood from the reservoir to the artery of the patient
  • a blood supply pump provided on the blood supply line and serving as an artificial heart.
  • the amount of blood circulation through the body is controlled by the operator through manual procedures for driving the blood withdrawing pumn and blood supply pump and replenishing the blood reservoir with transfusion blood.
  • This mode of control involves many items of manipulation, and the system must be controlled itemwise promptly based on immediate judgment while watching incessantly changing conditions of the patient, i.e. arterial and venous blood pressures, measurement of amount of bleeding, amount of blood in the reservoir and electrocardiogram.
  • the operator must be trained for controlling the system. Additionally the operator suffers from much fatigue when the operation takes a prolonged period of time.
  • An object of the present invention is to provide a system for the extracorporeal circulation of the blood which is adapted to automatically control the blood supply to the body so that the arterial pressure will be maintained suitably in n required range.
  • Another object of the invention is to automatically control the amount of blood to be withdrawn from the body so that the venous pressure of the patient will be maintained at an approximately constant level.
  • Another object of the invention is to provide a system for the extracorporeal circulation of the blood which is adapted to control the amount of blood to be supplied to the body of the patient and the amount of blood to be withdrawn therefrom to keep the amount of circulation of the blood through the body approximately constant.
  • Another object of the invention is to smooth- ly effect a change from the spontaneous circulation of the blood by the cardiac force of the patient to the forced circulation of the blood by an extracorporeal system or a change reverse to the above.
  • Another object of the invention is to assist the intracorporeal circulation of the blood by an extracorporeal circulation system while the blood is being spontaneously circulated through the body by the cardiac force of the patient so that the intracorporeal circulation of the blood will not be interrupted even when the heart stops temporarily.
  • the system of this invention for the extracorporeal circulation of the blood comprises a blood withdrawing line, an artificial lung provided on the line, a reservoir for the blood withdrawn, a blood supply line for sending out the blood from the reservoir, a blood sunply pump provided on the blood supply line and serving as an artificial heart, means for detecting that the venous pressure has exceeded a predetermined upper limit level, a blood pressure transducer for measuring the arterial pressure, means for increasing the amount of blood to be withdrawn when the venous pressure has exceeded the upper limit level, and means for controlling the blood supply pump in response to an output from the blood pressure transducer to maintain the arterial pressure in a predetermined required range.
  • the venous pressure detecting means comprises a vertical tube having an upper end opened to the atmosphere and a blood sensor provided at a position of specified height for the vertical tube for detecting that the blood level has reached the position.
  • This arrangement detects the venous pressure more accurately than a blood pressure transducer used as the venous pressure detecting means.
  • two vertical tubes may be used which are in communication with each other at upper portions thereof. When the blood in one of the vertical tubes rises beyond the communicating portion, the blood flows over this nortion into the other tube. The overflow is detected by a sensor. If the vertical tube or sensor is movable upward or downward, the upper limit level of the venous pressure is variable.
  • the venous pressure to be detected is preferably the central venous pressure.
  • the means for controlling the blood supply pump preferably comprises an upper limit detecting circuit for detecting that the arterial pressure has exceeded a predetermined upper limit value, a lower limit detecting.circuit for detecting that the arterial pressure has lowered below a predetermined lower limit value, and a control circuit for stopping the blood supply pump upon detecting the upper limit and for operating the blood supply pump upon detecting the lower limit. It is preferable to use a pulsatile pump as the blood supply pump.
  • the system of this invention for extracorporeal blood circulation includes a blood withdrawing line 1, an overflow line 2, an aspiration line 3 and a blood supply line 4.
  • These lines 1 to 4 are each made of a flexible tube.
  • the lines 1 to 3 are provided with rotary pumps 11 to 13 respectively.
  • the rotary pump comprises rollers adapted for a circular motion to draw and forward the blood through the tube by squeezing the tube, forming a continuous flow of blood.
  • the line 4 is provided with a pulsatile pump 14 which is operated by compressed air supplied thereto intermittently to intermittently force the blood through the line 4 as a pulsating flow.
  • the line 1 for withdrawing the venous blood from the body oi' the patient has two cannulas 15 connected to one end thereof.
  • the cannula 15 comprises an outer tube 16 having a slightly tapered forward end, and an inner tube 17 having a forward end projecting outward from the forward end of the outer tube 16 and a rear end extending outward from the outer tube 16.
  • the forward end of the outer tube 16 is formed with a large number of holes 18.
  • the rear end of the outer tube 16 is connected to the line 1.
  • the forward ends of the cannulas 15 are inserted into the superior and inferior venae cavae of the patient individually to draw the venous blood into the line 1 through the holes 18 and the outer tubes 16.
  • the line 1 is provided with an oxygenerator and a heat exchanger 6.
  • the oxygenerator functions as an artificial lung, in which the venous blood withdrawn from the body of the patient gives off carbon dioxide and takes up oxygen.
  • the heat exchanger maintains the blood at the desired temperature and, when needed, lowers the blood temperature. The blood thus refreshed is led into a blood reservoir 7 and stored therein.
  • the heat exchanger may be disposed between the reservoir 7 and the pump 14 on the blood supply line 4, or on a portion of the line 4 downstream from the pump 14.
  • a collapsible bag 9 for checking whether or not the blood is being withdrawn smoothly is nrovided on the blood withdrawing line 1 at a location between the shunt line 5 to be described later and the cannulas 15.
  • the bag 9 When the withdrawn blood is flowing smoothly through the line 1, the bag 9 is filled with the blood and is thereby inflated. If the line 1 is collapsed somewhere between the cannulas 15 and the bag 9, or if the blood is not withdrawn from the body for one reason or another, no blood is supplied to the bag 9. Since the blood in the line 1 is drawn by the pump 11 which is in operation at all times, the bag 9 is emptied of the blood and collapses. A sensor 27 is provided for detecting the state of the bag 9, i.e. whether the bag 9 is inflated or collapsed. The detecting signal of the sensor 27 is fed to a control unit 40. If the bag 9 collapses, an alarm goes on, informing the operator of the trouble occurring in the blood withdrawing line 1.
  • the blood supply pump 14 may be brought out of operation in the event of the line 1 malfunctioning. In the present embodiment, however, the pump 14 need not be stopped even if the line 1 is blocked since the blood is withdrawn through the overflow line 2 provided in parallel with the line 1.
  • a bottom portion of the blood reservoir 7 is connected by a shunt line 5 to a portion of the line 1 upstream from the pump 11.
  • the line 5 has an electromagnetic valve 32.
  • the valve 32 and the electromagnetic valve 33 to be described later are each a D inch valve.
  • the valve 32 When the valve 32 is open, the blood in the reservoir 7 is aspirated by the pump 11 through the line 5 and returned to the reservoir 7 by way of the oxygenerator and heat exchanger 6. Since a major portion of the blood drawn and forwarded by the pump 11 is supplied via the line 5, the amount of venous blood withdrawn from the body is small when the valve 32 is open.
  • the valve 32 is closed, no blood is supplied through the line 5, with the result that the suction by the pump 11 acts entirely on the cannula 15 to withdraw an increased amount of venous blood from the patient.
  • the overflow line 2 is provided with a unit 20 for adjusting the central venous pressure (hereinafter referred to as "CVP"), which is the mean pressure of the superior vena cava pressure and the inferior vena cava pressure and is given by the inner tubes 17 of the pair of cannulas 15.
  • CVP central venous pressure
  • the CVP adjusting unit 20 comprises a support member 23 the position of which is vertically adjustable, and two vertical tubes 21 and 22 mounted on the support member 23.
  • the vertical tube 21 is connected at its lower end to the inner tubes 17 of the two cannulas 15, while the lower end of the other vertical tube 22 is in communication with the inlet of the pump 12.
  • the upper end of the vertical tube 21 communicates through a horizontal tube with an upper portion of the vertical tube 22, which has an upper end extending upward beyond the communicating portion and opened to the atmosphere.
  • a sensor 24 for detecting an overflow of blood is disposed at a location slightly below the communicating portion of the vertical tube 22.
  • Each of the sensor 24, the above-mentioned sensor 27, and the sensors 25, 26 to be described later is a photoelectric detector, for which infrared rays are preferably used as the beam to be projected.
  • Other sensors such as those utilizing ultrasonic waves or capacitance, are of course usable.
  • the forward ends of the inner tubes 17 of the cannulas 15 are inserted into the superior and inferor venae cavae individually as already stated, portions of the venous blood flow into the inner tubes 17 individually from the two venae cavae and join together, whereby the blood pressures of the two veins are averaged.
  • the venous blood rises through the vertical tube 21 in accordace with the mean blood pressure, i.e. the CVP.
  • the level of the blood in the vertical tube 21 represents the CVP.
  • the upper limit level of CVP is determined by the height of the upper end of the vertical tube 21 from the heart of the patient.
  • the upper limit level of CVP can be set to a desired value by adjusting the level of the support member 23.
  • the aspiration line 3 is provided for aspirating the blood released from the site of the patient operated on.
  • the blood is sent to the reservoir 7 by the pump 13.
  • the blood through the lines 2 and 3, although led directly into the reservoir in Fig. 1, may be fed to the oxygenerator and heat exchanger 6 and then forwarded to the reservoir 7 when so required.
  • the blood supply line 4 has one end connected to a bottom portion of the reservoir 7 and the other end connected to a cannula which is inserted into the ascending aorta of the patient.
  • the refreshed blood stored in the reservoir 7 is passed through the line 4 into the aorta by the pulsatile pump 14 which is an artificial heart.
  • the blood through the line 4 is pulsatile and therefore resembles the arterial blood forced out from the heart to produce a physiologically favorable influence on the patient.
  • a reservoir 8 disposed above the blood reservoir 7 for storing the blood to be transfused has a bottom nortion connected to an upper portion of the reservoir 7 by a tube 37.
  • the tube 37 has an electromagnetic valve 33.
  • the sensor 25 detects that only a small amount of blood remains in the reservoir 7, while the sensor 26 detects that the reservoir 7 is filled with the blood to its upper limit level.
  • the electromagnetic valve 33 is opened to supply the blood from the reservoir 8.
  • the valve 33 is closed to discontinue the supply of blood.
  • the blood in the reservoir 8 may be supplied to the reservoir 7 by way of the oxygenerator and heat exchanger 6.
  • the reservoir'8 may be connected to the aspiration line 3. Ringer's solution and other solutions or drugs needed for the patient under operation are admixed with the blood in the reservoir 7.
  • an artificial kidney (not shown) is provided for filtering off such components from the blood in the reservoir 7 when the blood is diluted with these solutions to an excessive volume.
  • the compressed air for driving the pulsatile pump 14 is supplied from an air source through a line 34, which is provided with a pressure regulator 36, tank 35 and electromagnetic valve 31. As will be stated later, the valve 31 is controlled to open and close intermittently.
  • the control unit 40 controls the electromagnetic valves 31, 32 and 33.
  • the unit 40 receives detecting signals from the sensors 24, 25, 26 and 27, output signals from blood pressure transducers 41 and 42 for detecting the venous blood pressure and the arterial blood pressure (hereinafter referred to as "VP" and "AP” respectively) of the patient, output signals from an electrocardiograph 43 for preparing an electrocardiogram for the patient, and output pulses from a heat rate generator 44.
  • the blood pressure transducers 41 and 42 measure the blood pressures of the vena cava and the aorta respectively.
  • the blood pressures of the superior and inferor venae cavae may be measured individually, and the mean value of the measurements may be used as the VP (i.e. CVP).
  • Fig. 2 shows the construction of the control unit 40 in detail.
  • the signals of the transducer 42 representing the AP and those of the electrocardiograph 43 are sent to a monitor 45 equipped with a cathode-ray tube (CRT), on which the waveform of AP and the electrocardiogram are displayed. While the heart of the patient is in operation, the blood is circulated through the body by the force of cardiac contraction.
  • CTR cathode-ray tube
  • This mode of blood circulation is termed “spontaneous circulation.”
  • the intracorporeal circulation of the blood by the extracorporeal system of this invention, particularly by the pulsatile pump 14, is termed “forced circulation.”
  • the forced circulation can be effected by the pump 14 also during the spontaneous circulation because there is the need to assist in the blood circulation by the pump 14 when the spontaneous circulation is to be changed over to the forced circulation and vice versa, whereby the change-over can be accomplished smoothly.
  • the AP signal from the blood pressure transducer 42 and the output signal from the electrocardiograph 43 are used as triggers for starting the pump 14 during the spontaneous circulation.
  • a trigger generating circuit 46 produces a trigger pulse when the AP signal waveform has reached a peak.
  • a trigger generating circuit 47 produces a trigger pulse upon the rise of R wave in the electrocardiogram.
  • the operator can select one of the two trigger pulses by a selecting switch 48.
  • the selected trigger pulse is sent to an AND circuit 54 and to a timer 51.
  • the heart rate generator 44 For the forced circulation, the heart rate generator 44 produces trigger pulses of frequency set by its setting device 44a. The heart rate can be set as desired by the setting device 44a. The trigger pulse from the generator 44 is fed to an AND circuit 55. A switch 49 is used for setting the forced circulation. When the forced circulation is set by the switch 49, a high (H) level signal is given to an OR circuit 52.
  • H high
  • the timer 51 is reset by the trigger pulse of the generating circuit 46 or 47. If the timer 51 is not reset again upon lapse of a predetermined period of time, e.g. 2 seconds, after resetting, the timer produces an H level signal, which is fed to the OR circuit 52.
  • a predetermined period of time e.g. 2 seconds
  • the OR circuit 52 produces an H level signal, which is delivered tothe AND circuit 55.
  • the trigger pulse from the heart rate generator 44 passes through the AND circuit 55 and then through an OR circuit 56 and is fed to a delay circuit 57.
  • the H level signal from the OR circuit 52 is inverted by a NOT circuit 53 to a low (L) level signal, which is given to the AND .circuit 54.
  • the AND circuit 54 inhibits passage of the trigger pulse from the switch 48. If forced circulation is not set, and the heart is repeating contraction with a period of within 2 seconds, the output of the OR circuit 52 is at Llevel, and the output of the NOT circuit 53 is at H level. In this case, the trigger pulse from the generating circuit 46 or 47 passes through the AND circuit 54 and is fed to the delay circuit 57 through the OR circuit 56.
  • the AND circuit 55 prevents passage of the trigger pulse from the generator 44.
  • the delay circuit 57 delays the trigger pulse fed thereto for a predetermined period of time. This is of importance during spontaneous circulation. In the case of spontaneous circulation, the pump 14 for supplying the blood assists the heart of the patient in supplying the blood, so that the two blood supplies must be in synchronism. It is preferable that the pump 14 supply the blood with a time delay after the arterial blood is supplied by the heart. This is termed "counter pulsation.”
  • the delay circuit 57 determines this delay time, which is preferably so determined as to be dependent on the period of systole of the heart. The delay time is obtained, for example, by multiplying the previous period of systole measured or the mean value of preceding periods of systole by a suitable percentage. The measurement of the period and the calculation of the delay time can of course be performed automatically by a control circuit (not shown). The percentage is variable as desired.
  • the width of the delayed trigger pulse is shaped to resemble the systole time of the heart by a pulse width settina circuit 58.
  • the control pulse delivered from the circuit 58 is sent through AND circuits 59 and 60 to the electromagnetic valve 31 to open the valve.
  • the valve 31, when opened, permits supply of compressed air to the pump 14 to contract the pump 14 and supply the blood.
  • the width of the output pulse of the circuit 58 determines the contraction time of the pump 14.
  • the contraction time corresponds to the systole time of the heart.
  • the pulse width is calculated also based on the period of systole of the heart.
  • the delay time of the circuit 57 and the pulse width of the circuit 58 are determined preferably in accordance with the heart rate set by the generator 44.
  • the AP is used also for controlling the start and discontinuance of the operation of the pulsatile pump 14.
  • the AP signal from the blood pressure transducer 42 is applied to a peak hold circuit 61 and a mean value calculating circuit 62. While the heart of the patient is in operation and also while the pump 14 is in operation, the arterial blood is pulsating. Accordingly the AP signal has a pulsatile waveform.
  • the peak value of the pulsatile AP signal corresponding to the highest value of the arterial blood pressure, is held by and sent out from the hold circuit 61.
  • the highest blood pressure signal is fed to an upper limit detecting circuit 63 and a lower limit detecting circuit 64.
  • An upper limit value e.g.
  • the up D er limit detecting circuit 63 150 mm Hg for the highest blood pressure is set on the up D er limit detecting circuit 63.
  • the circuit 63 emits an H level signal.
  • a lower limit value (e.g. 100 mm Hg) for the highest blood pressure is set on the lower limit detecting circuit 64. If the highest blood pressure input signal is below the lower limit value, the circuit 64 delivers an H level signal.
  • the upper limit value and the lower limit value are variable.
  • the detecting signal from the upper limit detecting circuit 63 is sent through an OR circuit 67 to the set input terminal of a flip-flop 69.
  • the detecting signal from the lower limit detecting circuit 64 is sent through an OR circuit 68 to the reset input terminal of the flip-flop 69.
  • the flip-flop 69 is initially reset. When the flip-flop 69 is reset, the inverted output thereof is at H level, and at this time, the control pulse of the circuit 58 is sent through the AND circuit 59 to the valve 31. When the flip-flop 69 is set, the inverted output thereof is at L level, so that the passage of the control pulse is prevented.
  • the pump 14 is brought out of operation when the highest AP value exceeds the upper limit value, whereas the pump 14 is initiated into operation when the value drops below the lower limit value.
  • the highest AP value is always maintained at a level between the upper limit value and the lower limit value.
  • the mean value calculating circuit 62 is provided to meet such a situation.
  • the peak hold circuit 61 has the function of producing a no-peak signal when no pulse appears in the AF signal for a specified period of time.
  • the no-peak signal is applied to the calculating circuit 62, whereupon the circuit 62 functions to calculate and deliver the mean value of the AP signal every specified period of time.
  • the mean value signal is sent to upper and lower limit detecting circuits 65 and 66, on which upper and lower limit values are set respectively. When the mean value signal exceeds the upper limit value and when the signal drops below the lower limit value, the circuits 65 and 66 each produce an H level detecting signal, which is fed to the flip-flop 69 in the same manner as above.
  • the detecting signal (H level) from the sensor 24 of the CVP adjusting unit 20 has its waveform shaped by a waveform shaping circuit-73 and then applied to the set input terminal of a flip-flop 74.
  • the VP signal from the blood pressure transducer 41 is fed to a mean value calculating circuit 71, in which the mean value thereof is calculated every specified time interval.
  • the mean value signal is delivered to a lower limit detecting circuit 72, on which a lower limit value for the venous blood pressure is set.
  • the circuit 72 emits an H level detecting signal, which is given to the reset input terminal of the flip-flop 74.
  • the flip-flop 74 is initially reset.
  • the inverted out-cut sirnal thereof is at H level.
  • the E level signal orens the electromagnetic valve 32.
  • the flip-flop 74 When the flip-flop 74 is set by an overflow detecting signal from the sensor 24, the flip-flop delivers an inverted output at I level to close the valve 32. Consequently the pump 11 withdraws an increased amount of blood as already described.
  • the CVP exceeds the upper limit level (e.g. 10 to 20 mm Hg), for example, due to the congestion of blood in the body, the valve 32 closes, whereas if the mean VP value drops below the lower limit value (e.g. several mm Hg), the valve 32 opens.
  • the CVP is therefore maintained at an approximately constant level at all times.
  • the blood pressure transducer 41 and the circuits 71 and 72 are not always necessary; the valve 32 may be controlled only with the detecting signal of the sensor 24 .
  • the electromagnetic valve 32 is held open at all times and is closed only while the sensor is detecting an overflow, whereby the CVP can be kept approximately constant if the upper limit for the CVP is set at a suitable level.
  • the detecting signals from the sensors 25 and 26 are fed to a valve control circuit 81.
  • the circuit 81 emits an H level signal to open the valve 33 until the sensor 26 gives an upper limit level detecting signal.
  • the H level signal is sent through a NOT circuit 82 to the AND circuit 60. Accordingly when the blood remaining in the reservoir is found to be in a small amount, the control pulse from the circuit 58 does not pass the AND circuit 60, and the motor 14 comes to a stop. This prevents air from flowing into the artery of the patient.
  • the level to be detected by the sensor 25 is set at a relatively high level, the pump 14 need not always be stopped even if the sensor 25 emits a detecting signal.
  • Figs. 4, 5 and 6 show other examples of CVP adjusting units.
  • a vertical tube 21 has an extension 21a extending vertically beyond the portion thereof communicating with a vertical tube 22.
  • the extension 21a communicates at its upper end with the tube 22.
  • a sensor 24 may be disposed in the vicinity of the communicating portion of the vertical tube 21.
  • Fig. 5 shows pairs of vertical tubes 21A, 22A; 21E, 221; and 21C, 22C.
  • the vertical tubes 21A to 21C have communicating portions at different levels.
  • the other vertical tubes 22A to 22C are provided with sensors 24A to 24C for detecting an overflow of the blood, respectively.
  • a plurality of CVP measuring levels can be set on this CVP adjusting unit.
  • the detecting signals from the sensors 24A to 24C are used for controlling the opening degree of the valve 32, the CVP is controllable in a finer more accurate manner.
  • the vertical tubes 22A, 22B are provided with electromagnetic valves 38A, 38B, respectively. These valves 38A, 38B are open usually and are closed when the corresponding sensors 24A, 24P have detected an overflow of blood. The valves are opened again when the CVP lowers to eliminate the overflow.
  • the overflow line 2 shown in Fig. 6 is provided only with a vertical tube 21 the upper end of which is open to the atmosphere.
  • the line 2 has an electromagnetic valve 39 positioned closer to the pump 12.
  • the vertical tube 21 is fixed in place, while a sensor 24 is movable upward or downward along the tube 21 as supported on the tube.
  • the valve 39 is closed usually but is opened when the sensor 24 detects the blood reaching the level of the sensor.
  • the upper limit level for the CVP is settable as desired by varying the level of the sensor 24.
  • Fig. 7 shows another example of blood supply line.
  • the blood supply line 4 is provided with a rotary pump 91 and an electromagnetic valve 93 positioned downstream from the pump 91.
  • a return line is connected to the line 4, with another electromagnetic valve 92 provided on the return line.
  • the pumps 91, 14 operate, and the valve 92 is closed with the valve 93 opened, whereby the blood in the reservoir 7 is aspirated by the pump 91 and intermittently forced out by the pump 14.
  • the valve 92 is opened and the valve 93 is closed, so that the blood circulates through the return line and the pump 91 without flowing into the pump 14.
  • the pump 14 may be in or out of operation.
  • the valve 92 is closed again and the valve 93 is opened.
  • LAP left atrium
  • the LAP reflects the function of the left heart system
  • the CVP reflects the function of the right heart system.
  • the range of desired values of LAP e.g. 8 to 15 mm Hg is predetermined, and the CVP is so adjusted that the LAP will be maintained in this range at all times.
  • the LAP is detected by a pressure transducer 101.
  • the means LAP value is calculated at a specified time interval by a mean value calculating circuit 102.
  • the upper limit value e.g. 15 mm Hg
  • the lower limit value e.g. 8 mm Hg
  • the circuit 104 emits a lower limit detecting signal.
  • Level control means 105 raises or lowers the upper limit level of CVP in the CVP adjusting unit 20.
  • the vertical tubes 21, 22 and the support member 23 are raised or lowered.
  • the blood sensor 24 is raised or lowered.
  • the upper limit level for CVP is slowly lowered until the LAF lowers below the upper limit value.
  • the upper lirit level for the CVP is slowly raised. The rise of the CVP upper limit level is stopped when the LAP exceeds the lower limit value. In this way, the LAP is maintained in the desired range at all times.

Landscapes

  • Health & Medical Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Engineering & Computer Science (AREA)
  • Cardiology (AREA)
  • Hematology (AREA)
  • Anesthesiology (AREA)
  • Biomedical Technology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Vascular Medicine (AREA)
  • Mechanical Engineering (AREA)
  • Medical Informatics (AREA)
  • Pulmonology (AREA)
  • Emergency Medicine (AREA)
  • External Artificial Organs (AREA)
EP81107648A 1981-09-25 1981-09-25 Système pour la circulation extracorporelle du sang Expired EP0075606B1 (fr)

Priority Applications (5)

Application Number Priority Date Filing Date Title
US06/305,381 US4466804A (en) 1981-09-25 1981-09-24 Extracorporeal circulation of blood
EP88106528A EP0309642A1 (fr) 1981-09-25 1981-09-25 Système de circulation extracorporelle
EP81107648A EP0075606B1 (fr) 1981-09-25 1981-09-25 Système pour la circulation extracorporelle du sang
DE8181107648T DE3175734D1 (en) 1981-09-25 1981-09-25 System for extracorporeal circulation of blood
EP84114264A EP0150314A3 (fr) 1981-09-25 1981-09-25 Système de circulation sanguine extracorporelle

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
EP81107648A EP0075606B1 (fr) 1981-09-25 1981-09-25 Système pour la circulation extracorporelle du sang
EP84114264A EP0150314A3 (fr) 1981-09-25 1981-09-25 Système de circulation sanguine extracorporelle

Related Child Applications (3)

Application Number Title Priority Date Filing Date
EP84114264A Division EP0150314A3 (fr) 1981-09-25 1981-09-25 Système de circulation sanguine extracorporelle
EP84114264.9 Division-Into 1984-11-26
EP88106528.8 Division-Into 1988-04-22

Publications (2)

Publication Number Publication Date
EP0075606A1 true EP0075606A1 (fr) 1983-04-06
EP0075606B1 EP0075606B1 (fr) 1986-12-30

Family

ID=26081192

Family Applications (1)

Application Number Title Priority Date Filing Date
EP81107648A Expired EP0075606B1 (fr) 1981-09-25 1981-09-25 Système pour la circulation extracorporelle du sang

Country Status (2)

Country Link
US (1) US4466804A (fr)
EP (1) EP0075606B1 (fr)

Cited By (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0162447A2 (fr) * 1984-05-23 1985-11-27 TERUMO KABUSHIKI KAISHA trading as TERUMO CORPORATION Appareil détectant le volume de sang contenu dans un récipient
EP0217964A1 (fr) * 1985-04-05 1987-04-15 Kureha Kagaku Kogyo Kabushiki Kaisha (also called: Kureha Chemical Industry Co. Ltd.) Appareil medical a pompe
WO1987002894A2 (fr) * 1985-11-12 1987-05-21 Electro-Catheter Corporation Dispositif externe d'assistance cardiaque pulsatile
WO1999015213A1 (fr) * 1997-09-22 1999-04-01 Werner Mohl Dispositif d'assistance de l'effort cardiaque
US8255050B2 (en) 2007-02-27 2012-08-28 Miracor Medical Systems Gmbh Catheter to assist the performance of a heart
CN104321091A (zh) * 2012-09-28 2015-01-28 甘布罗伦迪亚股份公司 体外血液处理装置及其控制方法
US9770546B2 (en) 2012-09-28 2017-09-26 Gambro Lundia Ab Apparatus and method of controlling an extracorporeal blood treatment

Families Citing this family (79)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPS5883966A (ja) * 1981-11-13 1983-05-19 テルモ株式会社 膜型人工肺用血液回路
US4551131A (en) * 1983-05-02 1985-11-05 Thoratec Laboratories Corporation Autotransfusion system with anticoagulant delivery system
US4747826A (en) * 1983-06-08 1988-05-31 University Of Pittsburgh Rapid venous infusion system
JPS60142859A (ja) * 1983-12-29 1985-07-29 泉工医科工業株式会社 拍動血流量自動設定機構付ロ−ラポンプ
US4710164A (en) * 1984-05-01 1987-12-01 Henry Ford Hospital Automated hemodialysis control based upon patient blood pressure and heart rate
US4650457A (en) * 1985-08-16 1987-03-17 Kuraray Co., Ltd. Apparatus for extracorporeal lung assist
US4828543A (en) * 1986-04-03 1989-05-09 Weiss Paul I Extracorporeal circulation apparatus
US4902276A (en) * 1986-06-09 1990-02-20 The Regents Of The University Of California Apparatus and method for removing obstructions in bodily organs or cavities
US5527274A (en) * 1986-06-09 1996-06-18 Development Collaborative Corporation Catheter for chemical contact dissolution of gallstones
US4730936A (en) * 1986-10-10 1988-03-15 The United States Of America As Represented By The Secretary Of The Air Force Gas driven system for preparing large volumes of non-oxidized, pyridoxylated, polymerized stroma-free hemoglobin solution for use as a blood substitute
US4767399A (en) * 1986-12-05 1988-08-30 Fisher Scientific Group Inc. Dba Imed Corporation Volumetric fluid withdrawal system
US4874359A (en) * 1987-12-14 1989-10-17 White Frederick R Power infuser
US5069661A (en) * 1988-05-18 1991-12-03 Brigham And Women's Hospital Circulatory support system
US4994026A (en) * 1988-08-31 1991-02-19 W. R. Grace & Co.-Conn. Gravity flow fluid balance system
US5382407A (en) * 1988-12-14 1995-01-17 Minnesota Mining And Manufacturing Company Membrane blood oxygenator
US5270004A (en) * 1989-10-01 1993-12-14 Minntech Corporation Cylindrical blood heater/oxygenator
US5158534A (en) * 1990-07-03 1992-10-27 Cardiopulmonics, Inc. Automated gas delivery system for blood gas exchange devices
JP2974429B2 (ja) * 1991-02-04 1999-11-10 徹 新里 血液浄化装置
US5330420A (en) * 1992-01-13 1994-07-19 Therakos, Inc. Hemolysis detector
US5454374A (en) * 1992-01-17 1995-10-03 Omachi; Rodney S. Pressure-measuring method and needle system for hemodialysis
US5391142A (en) * 1992-07-29 1995-02-21 Organetics, Ltd. Apparatus and method for the extracorporeal treatment of the blood of a patient having a medical condition
US5458566A (en) * 1993-03-24 1995-10-17 Haemonetics, Inc. Reservoir volume sensing systems for autologous blood recovery
US5645531A (en) * 1993-05-26 1997-07-08 Quest Medical, Inc. Constant pressure blood mixture delivery system and method
US5573502A (en) * 1993-05-26 1996-11-12 Quest Medical, Inc. Display panel and controls for blood mixture delivery system
US5385540A (en) * 1993-05-26 1995-01-31 Quest Medical, Inc. Cardioplegia delivery system
US6607698B1 (en) 1997-08-15 2003-08-19 Therox, Inc. Method for generalized extracorporeal support
US6676900B1 (en) 1994-12-09 2004-01-13 Therox, Inc. Method for the preparation and delivery of gas-enriched fluids
US5702358A (en) * 1995-02-23 1997-12-30 Sorin Biomedical Inc. Cardioplegia delivery apparatus and method of use
JP3256157B2 (ja) * 1996-01-25 2002-02-12 天野 繁久 人工心肺装置
US5770073A (en) * 1996-03-15 1998-06-23 Minntech Corporation Combined cardiotomy and venous reservoir
US6048363A (en) * 1997-05-13 2000-04-11 Nagyszalanczy; Lorant Centrifugal blood pump apparatus
DE19746377C1 (de) * 1997-10-21 1999-07-01 Fresenius Medical Care De Gmbh Blutbehandlungsvorrichtung mit einer Einrichtung zur kontinuierlichen Überwachung des Blutdrucks des Patienten
US6602467B1 (en) 1998-07-24 2003-08-05 Therox, Inc. Apparatus and method for blood oxygenation
US6890482B2 (en) 1999-09-30 2005-05-10 Therox, Inc. Apparatus for blood oxygenation
US6759008B1 (en) 1999-09-30 2004-07-06 Therox, Inc. Apparatus and method for blood oxygenation
US6387324B1 (en) 1999-09-30 2002-05-14 Therox, Inc. Apparatus and method for blood oxygenation
US7008535B1 (en) 2000-08-04 2006-03-07 Wayne State University Apparatus for oxygenating wastewater
US6613280B2 (en) 2001-03-20 2003-09-02 Therox, Inc. Disposable cartridge for producing gas-enriched fluids
US6582387B2 (en) 2001-03-20 2003-06-24 Therox, Inc. System for enriching a bodily fluid with a gas
US7597666B2 (en) * 2001-07-30 2009-10-06 Stanley Frinak Access pressure ratio device and testing method
US8974394B2 (en) 2001-07-30 2015-03-10 Henry Ford Health System Device and method for detecting irregular placement of an extracorporeal vascular access needle
US8348850B2 (en) * 2001-07-30 2013-01-08 Henry Ford Health System Method of monitoring dislodgement of venous needles in dialysis patients
US20050085762A1 (en) * 2003-03-31 2005-04-21 Venkataramana Vijay Perfusion circuit for cardiopulmonary bypass with air removal system
US6852280B2 (en) 2003-03-31 2005-02-08 Venkataramana Vijay Condensed perfusion circuit for cardiopulmonary bypass and cardioplegia
US7455812B2 (en) * 2003-10-16 2008-11-25 Rheoxtech, Llc Method and apparatus for controlled reoxygenation
GB2408455A (en) * 2003-11-28 2005-06-01 Martin Lister Temporary heart
WO2006047147A1 (fr) * 2004-10-22 2006-05-04 Cobe Cardiovascular, Inc. Systemes de perfusion sanguine extracorporel convertible
US7458952B2 (en) * 2004-11-18 2008-12-02 Venkataramana Vijay Integrated cardiopulmonary bypass system for open and closed bypass circuits
EP1661592B1 (fr) * 2004-11-24 2008-05-28 LIFEBRIDGE Medizintechnik AG Dispositif pour fournir un circuit sanguin extracorporel
US8834399B2 (en) * 2010-12-07 2014-09-16 Zoll Lifebridge Gmbh Cardiopulmonary apparatus and methods for preserving organ viability
US7887502B2 (en) 2006-09-15 2011-02-15 University Of Florida Research Foundation, Inc. Method for using photoplethysmography to optimize fluid removal during renal replacement therapy by hemodialysis or hemofiltration
US9308307B2 (en) 2007-09-13 2016-04-12 Fresenius Medical Care Holdings, Inc. Manifold diaphragms
US9199022B2 (en) 2008-09-12 2015-12-01 Fresenius Medical Care Holdings, Inc. Modular reservoir assembly for a hemodialysis and hemofiltration system
US9358331B2 (en) 2007-09-13 2016-06-07 Fresenius Medical Care Holdings, Inc. Portable dialysis machine with improved reservoir heating system
US8597505B2 (en) 2007-09-13 2013-12-03 Fresenius Medical Care Holdings, Inc. Portable dialysis machine
US8240636B2 (en) 2009-01-12 2012-08-14 Fresenius Medical Care Holdings, Inc. Valve system
US20090101577A1 (en) * 2007-09-28 2009-04-23 Fulkerson Barry N Methods and Systems for Controlling Ultrafiltration Using Central Venous Pressure Measurements
US8105487B2 (en) 2007-09-25 2012-01-31 Fresenius Medical Care Holdings, Inc. Manifolds for use in conducting dialysis
EP2237814B1 (fr) 2007-11-29 2019-03-06 Fresenius Medical Care Holdings, Inc. Collecteur pour réaliser une hémodialyse et une hémofiltration
WO2010009421A1 (fr) 2008-07-17 2010-01-21 Rheoxtech, Llc Procédé et appareil pour atténuer une lésion par réoxygénation aiguë pendant une intervention coronarienne percutanée
WO2010042666A2 (fr) 2008-10-07 2010-04-15 Xcorporeal, Inc. Système et procédé d’amorçage pour systèmes de dialyse
CA2928208A1 (fr) 2008-10-30 2010-06-03 Fresenius Medical Care Holdings, Inc. Systeme de dialyse portatif modulaire
DE102009026592B4 (de) * 2009-05-29 2014-08-28 Sorin Group Deutschland Gmbh Vorrichtung zur Festlegung des venösen Zuflusses zu einem Blutreservoir eines extrakorporalen Blutkreislaufs
DE102009027195A1 (de) 2009-06-25 2010-12-30 Sorin Group Deutschland Gmbh Vorrichtung zur Förderung von Blut in einem extrakorporalen Kreislauf
US8888737B2 (en) 2009-10-20 2014-11-18 Rheoxtech, Llc Method and apparatus for cardiac tissue monitoring and catheter-based perfusion for mitigating acute reoxygenation injury
WO2012076632A1 (fr) 2010-12-07 2012-06-14 Lifebridge Medizintechnik Ag Procédé et système pour remplir et ventiler un dispositif pour traitement extracorporel de sang, avec noyage graduel d'un filtre
GB201110021D0 (en) 2011-06-15 2011-07-27 Newcastle Upon Tyne Hospitals Nhs Trust The Apparatus for performing haemodialysis
EP2754458B1 (fr) 2011-07-12 2017-02-01 Sorin Group Italia S.r.l. Réservoir de sang à double chambre
WO2013040182A1 (fr) 2011-09-13 2013-03-21 Quest Medical, Inc. Appareil et méthode de cardioplégie
US9201036B2 (en) 2012-12-21 2015-12-01 Fresenius Medical Care Holdings, Inc. Method and system of monitoring electrolyte levels and composition using capacitance or induction
US9157786B2 (en) 2012-12-24 2015-10-13 Fresenius Medical Care Holdings, Inc. Load suspension and weighing system for a dialysis machine reservoir
DE102013016469A1 (de) * 2013-10-04 2015-04-09 Fresenius Medical Care Deutschland Gmbh Blutbehandlungsvorrichtung und Verfahren zur Überwachung des Zustandes eines Abschnitts eines extrakorporalen Blutkreislaufs
US9354640B2 (en) 2013-11-11 2016-05-31 Fresenius Medical Care Holdings, Inc. Smart actuator for valve
EP3142719B1 (fr) 2014-05-16 2019-11-06 Sorin Group Italia S.r.l. Réservoir de sang à mesure de volume de fluide basée sur un capteur de pression
WO2018053461A1 (fr) 2016-09-19 2018-03-22 Henry Ford Health System Système et méthode de surveillance de délogement d'aiguilles veineuses chez des patients sous dialyse
WO2020259837A1 (fr) * 2019-06-27 2020-12-30 Livanova Deutschland Gmbh Dispositif pour établir automatiquement un afflux veineux vers un réservoir de sang d'un système de circulation de sang extracorporel
CN115515660A (zh) 2020-02-25 2022-12-23 奥科斯医疗公司 组合式血液泵和氧合器系统及相关方法
EP4483915A1 (fr) 2023-06-27 2025-01-01 BIOxy Med LLC-FZ Système combiné de pompe à sang et d'oxygénateur
EP4483916A1 (fr) 2023-06-27 2025-01-01 BIOxy Med LLC-FZ Système combiné de pompe à sang et d'oxygénateur

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3946731A (en) * 1971-01-20 1976-03-30 Lichtenstein Eric Stefan Apparatus for extracorporeal treatment of blood
DE2636290A1 (de) * 1976-08-12 1978-02-16 Fresenius Chem Pharm Ind Vorrichtung zur steuerung und ueberwachung des blutflusses bei der blutdialyse, -perfusion und -diafiltration unter benutzung nur einer anschlusstelle an den blutkreislauf des patienten (single-needle-technik)
DE2738164A1 (de) * 1976-10-18 1978-04-20 Baxter Travenol Lab Blutdruck-alarmvorrichtung fuer ein dialysegeraet
US4135496A (en) * 1976-01-30 1979-01-23 Institut Kardiologii Imeni A.L. Myasnikova Akademii Meditsinskikh Nauk Sssr Extracorporeal circulation apparatus
US4196729A (en) * 1977-12-23 1980-04-08 Cunningham Joseph N Device for perfusing a heart with blood supplied at constant pressure
EP0030760A1 (fr) * 1979-12-12 1981-06-24 Institut National De La Sante Et De La Recherche Medicale (Inserm) Dispositif de régulation du débit de sang délivré par un système de circulation extracorporelle, moyen de détection d'une quantité de liquide et élément inductif utilisé dans ce dispositif

Family Cites Families (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3590809A (en) * 1968-03-05 1971-07-06 Seymour B London Method for central venous pressure monitoring
US3890969A (en) * 1974-01-21 1975-06-24 Baxter Laboratories Inc Cardiopulmonary bypass system
US4175264A (en) * 1975-03-06 1979-11-20 Peter Schiff Electronic synchronizer-monitor system for controlling the timing of mechanical assistance and pacing of the heart
US4231354A (en) * 1978-07-14 1980-11-04 Howmedica, Incorporated Pulsatile blood pumping apparatus and method

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3946731A (en) * 1971-01-20 1976-03-30 Lichtenstein Eric Stefan Apparatus for extracorporeal treatment of blood
US4135496A (en) * 1976-01-30 1979-01-23 Institut Kardiologii Imeni A.L. Myasnikova Akademii Meditsinskikh Nauk Sssr Extracorporeal circulation apparatus
DE2636290A1 (de) * 1976-08-12 1978-02-16 Fresenius Chem Pharm Ind Vorrichtung zur steuerung und ueberwachung des blutflusses bei der blutdialyse, -perfusion und -diafiltration unter benutzung nur einer anschlusstelle an den blutkreislauf des patienten (single-needle-technik)
DE2738164A1 (de) * 1976-10-18 1978-04-20 Baxter Travenol Lab Blutdruck-alarmvorrichtung fuer ein dialysegeraet
US4196729A (en) * 1977-12-23 1980-04-08 Cunningham Joseph N Device for perfusing a heart with blood supplied at constant pressure
EP0030760A1 (fr) * 1979-12-12 1981-06-24 Institut National De La Sante Et De La Recherche Medicale (Inserm) Dispositif de régulation du débit de sang délivré par un système de circulation extracorporelle, moyen de détection d'une quantité de liquide et élément inductif utilisé dans ce dispositif

Cited By (29)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0162447A2 (fr) * 1984-05-23 1985-11-27 TERUMO KABUSHIKI KAISHA trading as TERUMO CORPORATION Appareil détectant le volume de sang contenu dans un récipient
EP0162447A3 (en) * 1984-05-23 1987-08-05 Terumo Kabushiki Kaisha Trading As Terumo Corporation Apparatus for detecting the volume of blood in a blood reservoir
EP0217964A1 (fr) * 1985-04-05 1987-04-15 Kureha Kagaku Kogyo Kabushiki Kaisha (also called: Kureha Chemical Industry Co. Ltd.) Appareil medical a pompe
EP0217964A4 (fr) * 1985-04-05 1987-07-30 Kureha Chemical Ind Co Ltd Appareil medical a pompe.
US5006111A (en) * 1985-04-05 1991-04-09 Kureha Kagaku Kogyo Kabushiki Kaisha Medical pump device and a method for compensating a deviation of a measured blood flow rate
WO1987002894A2 (fr) * 1985-11-12 1987-05-21 Electro-Catheter Corporation Dispositif externe d'assistance cardiaque pulsatile
WO1987002894A3 (fr) * 1985-11-12 1987-10-08 Electro Catheter Corp Dispositif externe d'assistance cardiaque pulsatile
GB2196854A (en) * 1985-11-12 1988-05-11 Electro Catheter Corp External pulsatile cardiac assist device
GB2196854B (en) * 1985-11-12 1990-02-14 Electro Catheter Corp External pulsatile cardiac assist device
WO1999015213A1 (fr) * 1997-09-22 1999-04-01 Werner Mohl Dispositif d'assistance de l'effort cardiaque
US6506146B1 (en) 1997-09-22 2003-01-14 Werner Mohl Apparatus for supporting heart performance
US11351356B2 (en) 2007-02-27 2022-06-07 Miracor Medical Sa Device to assist the performance of a heart
US11572879B2 (en) 2007-02-27 2023-02-07 Miracor Medical Sa Device to assist the performance of a heart
US12117007B1 (en) 2007-02-27 2024-10-15 Miracor Medical Sa Device to assist the performance of a heart
US12104600B2 (en) 2007-02-27 2024-10-01 Miracor Medical Sa Device to assist the performance of a heart
US11754077B1 (en) 2007-02-27 2023-09-12 Miracor Medical Sa Device to assist the performance of a heart
US11674517B2 (en) 2007-02-27 2023-06-13 Miracor Medical Sa Device to assist the performance of a heart
US8801590B2 (en) 2007-02-27 2014-08-12 Miracor Medical Systems Gmbh Catheter to assist the performance of a heart
US10251984B2 (en) 2007-02-27 2019-04-09 Miracor Medical Sa Catheter to assist the performance of a heart
US11376415B2 (en) 2007-02-27 2022-07-05 Miracor Medical Sa Device to assist the performance of a heart
US11123540B2 (en) 2007-02-27 2021-09-21 Miracor Medical Sa Device to assist the performance of a heart
US8255050B2 (en) 2007-02-27 2012-08-28 Miracor Medical Systems Gmbh Catheter to assist the performance of a heart
US11351357B2 (en) 2007-02-27 2022-06-07 Miracor Medical Sa Device to assist the performance of a heart
US10258733B2 (en) 2012-09-28 2019-04-16 Gambro Lundia Ab Apparatus and method of controlling an extracorporeal blood treatment
US9821106B1 (en) 2012-09-28 2017-11-21 Gambro Lundia Ab Apparatus for extracorporeal blood treatment and a control method therefor
US9770546B2 (en) 2012-09-28 2017-09-26 Gambro Lundia Ab Apparatus and method of controlling an extracorporeal blood treatment
US9750865B2 (en) 2012-09-28 2017-09-05 Gambro Lundia Ab Apparatus for extracorporeal blood treatment and a control method therefor
CN104321091B (zh) * 2012-09-28 2017-02-01 甘布罗伦迪亚股份公司 体外血液处理装置及其控制方法
CN104321091A (zh) * 2012-09-28 2015-01-28 甘布罗伦迪亚股份公司 体外血液处理装置及其控制方法

Also Published As

Publication number Publication date
US4466804A (en) 1984-08-21
EP0075606B1 (fr) 1986-12-30

Similar Documents

Publication Publication Date Title
US4466804A (en) Extracorporeal circulation of blood
US5820579A (en) Method and apparatus for creating pulsatile flow in a cardiopulmonary bypass circuit
JP7557511B2 (ja) 補助人工心臓およびその制御装置
US7494590B2 (en) Method of controlling a dialysis apparatus
CA1042747A (fr) Circulation extracorporelle
US5536237A (en) Blood extraction flow control calibration system and method
US4865581A (en) Retroperfusion control apparatus, system and method
EP0078090B1 (fr) Procédé et dispositif pour contrôler la pression de manchette lors de la mesure de la pression sanguine dans un doigt à l'aide d'un pléthysmographe photoélectrique
DE69124515T2 (de) Durchflussregelsystem für blutentnahme und reinfusion sowie entsprechendes verfahren
US6558340B1 (en) Dialysis machine, in particular for home use
US3513845A (en) Bypass heart pump and oxygenator system
EP1070511A1 (fr) Coeur artificiel auxiliaire facilitant le retablissement de la fonction cardiaque
JPS62500006A (ja) 完全携帯式、半自動機械式心肺機能代行装置およびその方法
EP0150314A2 (fr) Système de circulation sanguine extracorporelle
EP0273041A4 (fr) Systeme commande par ordinateur assurant une pression positive en fin d'expiration.
CA1209672A (fr) Systeme de circulation extracorporelle
US6024692A (en) Fluid circulator for nonlinear compliant circuits
US5115682A (en) Coronary artery graft flow-meter
DE102022004903A1 (de) Extrakorporale Kreislaufunterstützung mit Herzaktivität-optimierter Verzögerungszeit
SU1581323A1 (ru) Аппарат вспомогательного кровообращени
Tamari et al. A new bladder allows kinetic venous augmentation with a roller pump
Schneider et al. AUTOMATIC CONTROL OF PHASIC AORTIC PRESSURE IN THE EXPERIMENTAL ANIMAL
JPS647790B2 (fr)
JPS6464B2 (fr)
CS260838B1 (cs) Zařízení pro měření krevního tlaku a pulsu v mimotělním krevním obvodu při mimotělní očistě krve

Legal Events

Date Code Title Description
PUAI Public reference made under article 153(3) epc to a published international application that has entered the european phase

Free format text: ORIGINAL CODE: 0009012

AK Designated contracting states

Designated state(s): DE FR GB IT NL SE

17P Request for examination filed

Effective date: 19830916

RAP1 Party data changed (applicant data changed or rights of an application transferred)

Owner name: HINO, TSUNEKAZU

RAP1 Party data changed (applicant data changed or rights of an application transferred)

Owner name: OMRON TATEISI ELECTRONICS CO.

Owner name: HINO, TSUNEKAZU

RIN1 Information on inventor provided before grant (corrected)

Inventor name: HINO, TSUNEKAZU

GRAA (expected) grant

Free format text: ORIGINAL CODE: 0009210

AK Designated contracting states

Kind code of ref document: B1

Designated state(s): DE FR GB IT NL SE

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: IT

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT;WARNING: LAPSES OF ITALIAN PATENTS WITH EFFECTIVE DATE BEFORE 2007 MAY HAVE OCCURRED AT ANY TIME BEFORE 2007. THE CORRECT EFFECTIVE DATE MAY BE DIFFERENT FROM THE ONE RECORDED.

Effective date: 19861230

Ref country code: FR

Free format text: THE PATENT HAS BEEN ANNULLED BY A DECISION OF A NATIONAL AUTHORITY

Effective date: 19861230

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: SE

Effective date: 19861231

REF Corresponds to:

Ref document number: 3175734

Country of ref document: DE

Date of ref document: 19870205

EN Fr: translation not filed
PLBE No opposition filed within time limit

Free format text: ORIGINAL CODE: 0009261

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: NO OPPOSITION FILED WITHIN TIME LIMIT

26N No opposition filed
PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: DE

Payment date: 19901001

Year of fee payment: 10

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: GB

Payment date: 19910816

Year of fee payment: 11

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: NL

Payment date: 19910930

Year of fee payment: 11

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: DE

Effective date: 19920602

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: GB

Effective date: 19920925

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: NL

Effective date: 19930401

NLV4 Nl: lapsed or anulled due to non-payment of the annual fee
GBPC Gb: european patent ceased through non-payment of renewal fee

Effective date: 19920925